Processor controlled intraocular lens system

ABSTRACT

The present invention relates generally to an intraocular lens system controlled with a processor, including a liquid meniscus lens and supporting electronics. Embodiments may include intraocular lens systems of various shapes and sizes, liquid meniscus lens components of various shapes and sizes, variations in supporting electronics with corresponding variations in lens function.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims priority to Provisional U.S. Patent ApplicationSer. No. 61/529,350, filed on Aug. 31, 2011.

FIELD OF USE

The present invention relates generally to an intraocular lenscontrolled with a processor. Some specific embodiments include anintraocular lens with a liquid meniscus.

BACKGROUND

Since the mid-20^(th) century, intraocular lenses (IOLs) have beenimplanted in eyes, replacing a patient's natural crystalline lens thatis clouded by cataracts or changing the eye's optical power. Initially,IOLs were fixed monofocal lenses of a power to provide correction onlyfor distance vision. Even today, a majority of IOLs implanted during eyesurgery are monofocal, requiring a patient to wear glasses for nearvision correction.

More recent advances have included multifocal IOLs which provide apatient with correction for both distance and near vision. MultifocalIOLs employ the same technology as multifocal contact lenses, butimplemented within an intraocular lens.

Some IOLs currently claim adaptive capabilities, providing the patientwith limited visual accommodation. Accommodating IOLs are designed toallow the eye to shift focus onto near objects. Current versions ofaccommodating IOLs rely on physical changes within the eye to effect achange in the shape of an intraocular lens, resulting in a change in thelens' optical power. In many implementations, the optical properties ofaccommodating IOLs cannot be changed after implantation, although suchchanges may be desirable for a variety of reasons. In many cases, apatient's vision prescription changes as a result of the eye surgerynecessary to implant the IOL. The closure and healing of the incisionmay induce astigmatism as portions of the eye are drawn together toclose the incision. Further, as a patient ages and ciliary muscleswithin the eyes weaken, the eyes are no longer able to exert thenecessary force to change an IOL's shape and achieve the desired levelof accommodation. Finally, even a minor error in the initial IOLprescription will leave the patient with less than optimal vision.

More recently, it has been theorized that electronic components may beincorporated into an intraocular lens. Electronic components may enablean intraocular lens including a liquid meniscus lens which providesvariable focus that can be controlled and adjusted in a variety of ways.

SUMMARY

Accordingly, the present invention provides an intraocular lens systemcontrolled with a processor, including a liquid meniscus lens andsupporting electronics.

According to the present invention, an intraocular lens system includesan optical zone in which is found a liquid meniscus lens, and anelectrical zone with components such as power sources, processors,memory, sensors, and communication elements. Power sources within anintraocular lens system may be recharged or receive continuous chargeusing a variety of methods. The liquid meniscus lens, supported by powersources, sensors and logic within the intraocular lens system, providesautomated or manual focus capabilities, providing focus for near vision,far vision, and points in between. After surgical insertion, variouscapabilities of an intraocular lens system may be remotely adjusted,such as to correct for surgery-induced astigmatism, to adjustsensitivity of lens functions to changes in sensor data, and to alterthe range of diopter correction between far and near vision.

DESCRIPTION OF THE DRAWINGS

FIG. 1A illustrates a prior art example of a cylindrical liquid meniscuslens in a first state.

FIG. 1B illustrates the prior art example of a cylindrical liquidmeniscus lens in a second state.

FIG. 2 illustrates a profile sliced cut away of an exemplary arcuateliquid meniscus lens according to some embodiments of the presentinvention.

FIG. 3 illustrates a front view block diagram of an exemplaryintraocular lens system in the form of a rounded rectangle according tosome embodiments of the present invention.

FIG. 4 illustrates a front view block diagram of an exemplaryintraocular lens system in the form of an ellipse according to someembodiments of the present invention.

FIG. 5 illustrates a front view block diagram of an exemplaryintraocular lens system in the form of a circle according to someembodiments of the present invention.

FIGS. 6A, 6B and 6C illustrate various cross-sectional side views of anexemplary intraocular lens system according to some embodiments of thepresent invention.

DETAILED DESCRIPTION OF THE INVENTION

The present invention includes methods and apparatus for forming anintraocular lens system controlled by a processor. In particular, thepresent invention includes methods and apparatus for providing anintraocular lens system controlled by a processor, including a liquidmeniscus lens and supporting electronics. In some embodiments, thepresent invention includes a liquid meniscus lens in an optic zone withsupporting electronics located in an electrical zone around theperiphery.

In the following sections detailed descriptions of embodiments of theinvention will be given. The description of both preferred andalternative embodiments are exemplary embodiments only, and it isunderstood that to those skilled in the art that variations,modifications and alterations may be apparent. It is therefore to beunderstood that said exemplary embodiments do not limit the scope of theunderlying invention.

GLOSSARY

In this description and claims directed to the presented invention,various terms may be used for which the following definitions willapply:

Accommodation (and Accommodating IOL): as used herein refers to theprocess by which the eye changes optical power to maintain a clear image(focus) on an object as its distance changes.

Astigmatism: as used herein refers to faulty vision resulting fromdefective curvature of the cornea or lens of the eye.

Capsular Bag: as used herein refers to a sack-like structure remainingwithin the eye following removal of the natural lens. An implantedintraocular lens is placed within this structure to recreate the usualphakic (presence of the natural crystalline lens) state.

Ciliary Muscle: as used herein refers to a ring of striated smoothmuscle in the eye's middle layer (vascular layer) that controlsaccommodation for viewing objects at varying distances.

Diopter: as used herein refers to a unit of measure of the optical orrefractive power of a lens.

Electrical Zone: as used herein refers to an area around the peripheryof an optical zone in which electronic elements are found.

Intraocular Lens System: as used herein refers to an intraocular lensincluding supporting electronics and a liquid meniscus lens.

Intraocular Lens (IOL): as used herein refers to an implanted lens inthe eye, usually replacing the existing crystalline lens because it hasbeen clouded over by a cataract, or as a form of refractive surgery tochange the eye's optical power.

Liquid Meniscus Lens: as used herein refers to a lens containing one ormore fluids to create an infinitely-variable lens without any movingparts by controlling the meniscus (the surface of the liquid.)

Microprocessor: as used herein refers to a circuit or series of circuitscapable of receiving digital data and performing a calculation basedupon the data received.

Monofocal Lens: as used herein refers to a lens with a fixed focus forone distance.

Multifocal Lens: as used herein refers to a lens that has rings of focuspower variations. Some rings provide focus for near objects, some formid-range objects, and some rings provide the focus power for distantobjects.

Optical Zone: as used herein refers to an area of an ophthalmic lensthrough which a wearer of the ophthalmic lens sees. An ophthalmic lensmay include a contact lens or an intraocular lens.

Referring now to FIG. 1A, a cut away view of a prior art liquid meniscuslens 100 is illustrated with an oil 101 and a saline solution 102contained within cylinder 110. The cylinder 110 includes two plates ofoptical material 106. Each plate 106 includes a flat interior surface113-114. The cylinder 110 includes an interior surface that isessentially rotationally symmetric. In some prior art embodiments, oneor more surfaces may include a hydrophobic coating 103. Electrodes 105are also included on or about the perimeter of the cylinder. Anelectrical insulator 104 may also be used proximate to the electrodes105.

According to the prior art, each of the interior surfaces 113-114 isessentially flat or planar. An interface surface 112A is defined betweenthe saline solution 102 and the oil 101. As illustrated in FIG. 1A, theshape of the interface 112A is combined with the refractive indexproperties of the saline solution 102 and the oil 101 to receiveincident light 108 through a first interior surface 113 and providedivergent light 109 through a second interior surface 114. The shape ofthe interface surface between the oil 101 and the saline solution 102may be altered with the application of an electrical current to theelectrodes 105.

FIG. 100A illustrates a perspective view of the prior art liquidmeniscus lens illustrated at 100.

Referring now to FIG. 1B, the prior art liquid meniscus lens 100 isillustrated in an energized state. The energized state is accomplishedby applying voltage 114 across the electrodes 105. The shape of theinterface surface 112B between the oil 101 and the saline solution 102Bis altered with the application of an electrical current to theelectrodes 105. As illustrated in FIG. 1B, incident light 108B passingthrough the oil 101 and the saline solution 102B is focused into aconvergent light pattern 111.

Referring now to FIG. 2, a cut away view of a liquid meniscus lens 200with a front curve lens 201 and a back curve lens 202. The front curvelens 201 and the back curve lens 202 are positioned proximate to eachother and form a cavity 210 therebetween. The front curve lens 201includes a concave arcuate interior lens surface 203 and a convexarcuate exterior lens surface 204. The concave arcuate lens surface 203may have one or more coatings (not illustrated in FIG. 2). Coatings mayinclude, for example, one or more of electrically conductive materialsor electrically insulating materials, hydrophobic materials orhydrophilic materials. One or both of the concave arcuate lens surface203 and the coatings are in liquid and optical communication with an oil208 contained within the cavity 210.

The back curve lens 202 includes a convex arcuate interior lens surface205 and a concave arcuate exterior lens surface 206. The convex arcuatelens surface 205 may have one or more coatings (not illustrated in FIG.2). Coatings may include, for example, one or more of electricallyconductive materials or electrically insulating materials, hydrophobicmaterials or hydrophilic materials. At least one of the convex arcuatelens surface 205 and the coatings are in liquid and opticalcommunication with a saline solution 207 contained within the cavity210. The saline solution 207 includes one or more salts or othercomponents which are electrically conductive and as such may be eitherattracted to or repulsed by an electric charge.

According to the present invention, an electrically conductive coating209 is located along at least a portion of a periphery of one or both ofthe front curve lens 201 and the back curve lens 202. The electricallyconductive coating 209 may include gold or silver and is preferablybiocompatible. Application of an electrical charge to the electricallyconductive coating 209 creates either an attraction or a repulsion ofthe electrically conductive salts or other components in the salinesolution 207.

The front curve lens 201 has an optical power in relation to lightpassing through the concave arcuate interior lens surface 203 and aconvex arcuate exterior lens surface 204. The optical power may be 0 ormay be a plus or minus power. In some preferred embodiments, the opticalpower is a power typically found in corrective contact lenses or anartificial intraocular lens, such as, by way of non-limiting example, apower between −8.0 and +8.0 diopters.

The back curve lens 202 has an optical power in relation to lightpassing through the convex arcuate interior lens surface 205 and aconcave arcuate exterior lens surface 206. The optical power may be 0 ormay be a plus or minus power. In some embodiments, the optical power isa power typically found in corrective contact lenses or an artificialintraocular lens, such as, by way of non-limiting example, a powerbetween −8.0 and +8.0 diopters.

Various embodiments may also include a change in optical powerassociated with a change in shape of a liquid meniscus 211 formedbetween the saline solution 207 and the oil 208. In some embodiments, achange in optical power may be relatively small, such as, for example, achange of between 0 to 2.0 diopters of change. In other embodiments, achange in optical power associated with a change in shape of a liquidmeniscus may be up to about 30 or more diopters of change. Generally, ahigher change in optical power associated with a change in shape of aliquid meniscus 211 is associated with a relatively thicker lensthickness 213.

According to some embodiments of the present invention, such as thoseembodiments that may be included in an ophthalmic lens, such as acontact lens or an intraocular lens, a cross cut lens thickness 213 ofan arcuate liquid meniscus lens 200 will be up to about 1,000 micronsthick. An exemplary lens thickness 213 of a relatively thinner lens 200may be up to about 200 microns thick. Preferred embodiments may includea liquid meniscus lens 200 with a lens thickness 213 of about 600microns thick. Generally a cross cut thickness of front curve lens 201may be between about 35 microns to about 200 microns and a cross cutthickness of a back curve lens 202 may also be between about 35 micronsand 200 microns.

According to the present invention, an aggregate optical power is anaggregate of optical powers of the front curve lens 201, the back curvelens 202 and a liquid meniscus 211 formed between the oil 208 and thesaline solution 207. In some embodiments, an optical power of the lens200 will also include a difference in refractive index as between one ormore of the front curve lens 201, the back curve lens 202, oil 208 andthe saline solution 207.

In those embodiments that include an arcuate liquid meniscus lens 200incorporated into an ophthalmic lens, such as an intraocular lens and acontact lens it is additionally desirous for the saline 207 and oil 208to remain stable in their relative positions within the arcuate liquidmeniscus lens 200 as a wearer moves. Generally, it is preferred toprevent the oil 208 from floating and moving relative to the saline 207when the wearer moves, accordingly, an oil 208 and saline solution 207combination is preferably selected with a same or similar density.Additionally, an oil 208 and a saline solution 207 preferably haverelatively low immiscibility so that the saline solution 207 and oil 208will not mix.

In some preferred embodiments, a volume of saline solution 207 containedwithin the cavity 210 is greater than the volume of oil 208 containedwithin the cavity 210. Additionally, some preferred embodiments includethe saline solution 207 in contact with essentially an entirety of aninterior surface 205 of the back curve lens 202. Some embodiments mayinclude a volume of oil 208 that is about 66% or more by volume ascompared to an amount of saline solution 207. Some additionalembodiments may include an arcuate liquid meniscus lens 200 wherein avolume of oil 208 is about 90% or less by volume as compared to anamount of saline solution 207.

Referring now to FIG. 3, depicted is a front view block diagram of anintraocular lens system 300 with an optical zone 301 surrounded by anelectrical zone 302. In this embodiment, the intraocular lens system 300is in the shape of a rounded rectangle with a circular visual zone 301in the center. Other embodiments may include an optical zone 301 ofelliptical, rectangular, or other shape conducive to vision correction.In the present invention, the visual zone 301 consists of a liquidmeniscus lens. A liquid meniscus lens may be in a traditional “hockeypuck” form, as described in FIGS. 1A and 1B, or in an arcuate form, asdescribed in FIG. 2.

Around a perimeter of an optical zone 301 is an electrical zone 302 withsupporting components for operation and control of an intraocular lenssystem with a liquid meniscus lens. In some embodiments, electrical zone302 areas may be folded to facilitate insertion of the intraocular lenssystem into the eye during surgery. In preferred embodiments, anintraocular lens system may be encapsulated, in part or in whole,providing protection for supporting electronics and other sensitivecomponents. Encapsulation may be accomplished, by way of illustrativeexample, via one or more known flexible materials such as silicone,silicone elastomer, silicone hydrogel, or flourohydrogel.

Some preferred embodiments of the present invention include within anelectrical zone 302 self-contained power sources which autonomouslypower an intraocular lens system with liquid meniscus lens. In thiscase, self-contained power sources may be recharged infrequently, suchas only at night, or only every few days. In some alternativeembodiments, power sources are not self-contained, but are continuouslyor regularly recharged. Power sources may include, for example, one ormore batteries or other storage devices. In some preferred embodiments,the storage devices include one or more lithium ion batteries or otherrechargeable devices. Multiple power sources may be in an array and mayinclude redundant elements to maximize the possibility of fail-safeoperation.

Power sources may be charged by receiving and storing energy for currentor future use. Nighttime charging, or charging while a user is sleeping,may be accomplished in a variety of ways. In a preferred embodiment, theuser wears a sleep mask that emits a radio frequency or magnetic fieldfor charging. This embodiment may be especially desirable in the case ofradio frequency charging wherein radio frequency coils must be properlyaligned with features on the intraocular lens system to achievecharging. A sleep mask maintains consistent alignment relative to auser's eyes as the user moves during sleep. In another embodiment,charging elements may be in temporary patches placed on a user's bodyduring sleep, such as on their temple, forehead or cheekbone. If patchesare placed on a user's head, they offer the benefit of consistentalignment with intraocular lenses, similar to a sleep mask. Otherembodiments for sleep charging include a charging device contained in apillowcase, a pillow, a blanket, or other article on which or near whicha user sleeps. Additionally, far field charging may be accomplished byplacing a charging device, such as radio frequency emitter, on a user'snightstand or headboard.

In some embodiments, wake-time charging is achieved with chargingelements located in a user's eyeglasses or sunglasses frame emittingradio frequency or magnetic field. In other embodiments, continuouscharging may be accomplished with photo sensors in an electrical zone302 of an intraocular lens system. In this embodiment, light received byphoto sensors is converted to electrical energy and stored in powersources within the electrical zone 302. Light for photo sensor chargingmay be in the visible spectrum or outside the visible spectrum. In yetanother embodiment, a thermoelectric method may enable continuouscharging or trickle charging of power sources. For example a temperaturebetween the body temperature and an ambient temperature may be used togenerate a trickle charge and harvested energy is stored in powersources within the electrical zone 302.

Charging of power sources may be via one or a combination of the variousmethods which have been described. One example of combined chargingmethods includes radio frequency charging during sleep cycles coupledwith photo sensor trickle charging during wake cycles.

Some embodiments of the present invention include a power managementsubsystem supported by processor, memory and other components in anelectrical zone 302 of an intraocular lens system with liquid meniscuslens. A power management subsystem may perform various functions, suchas, for example, monitoring power usage and levels, managing thecharging of power sources, limiting lens functions when power levels arebelow a minimum threshold, switching to draw power from one or moreredundant power sources when others fail or fall below a specifiedthreshold, and monitoring power sources to determine when charging iscomplete so that charging can be terminated.

Power sources supply electrical current to a liquid meniscus lenscontained within an optical zone 301 of an intraocular lens system,wherein a change in the shape of the liquid meniscus results in a changein optical power, as described in FIG. 2. After receiving power, theliquid meniscus lens acts as a capacitor, holding a charge andmaintaining an activated position of the liquid meniscus, such asincreased optical power for near vision, without the continuousapplication of power. To revert to distance vision, power is dischargedfrom the liquid meniscus lens and the liquid meniscus assumes itsrelaxed position, providing the appropriate default optical power fordistance vision.

Power sources are under control of a microprocessor located within anelectrical zone 302. The microprocessor executes one or more programsthat analyze data and apply power accordingly to control operation ofthe intraocular lens system with liquid meniscus lens. In someembodiments, data analyzed by the microprocessor is in the form ofsensed data, such as, for example, sensing contraction within thecapsular bag, sensing a potential voltage change across a ciliarymuscle, and sensing patterns of eyelid closing or squinting whichsignify an intent to switch between near and distance vision.Contraction of the capsular bag may be sensed, for example, via apressure transducer. The transducer will translate a pressure changeinto one or both of an analog voltage or a digital voltage state.

In some preferred embodiments, a transducer may be used to detect avoltage change across a ciliary muscle. Eyelid and squinting movementsmay be sensed, for example, with optical sensors. Sensed data may bestored in memory and analyzed by a microprocessor to determineappropriate changes to the liquid meniscus lens.

In some embodiments, an intraocular lens system includes one or moreantennae in an electrical zone 302. Antennae may be used, by way ofnon-limiting example, to receive radio frequency for charging powersources, for receiving data from other sensors, and for communicationwith external devices and other devices within an intraocular lenssystem. Antennae may be of various shapes and sizes within an electricalzone 302 of an intraocular lens system.

An intraocular lens system with liquid meniscus lens may be modified intwo different ways: focus and adjustment. Its primary purpose is tochange focus, accommodating distance vision, near vision, andintermediate vision. In some embodiments, changes in focus areautomated, such as, for example, when a pressure transducer sensescontraction of the capsular bag, and a processor in the intraocular lenssystem translates the magnitude of capsular bag pressure into acorresponding optical power change within the liquid meniscus lens. Inother embodiments, changes in focus may be controlled manually, such as,for example, when a wearer presses a button on a fob, transmitting acommand to a processor in an intraocular lens system which in turninitiates an optical power change within a liquid meniscus lens.

Adjustment refers to one-time or ad-hoc modification of an intraocularlens system. Adjustment may, for example, set or modify the diopterchange between far and near vision, may program operation of a liquidmeniscus lens to correct for a specific degree and magnitude ofastigmatism, and may change the sensitivity of the intraocular lenssystem to changes in a ciliary muscle or capsular bag. Adjustment may beaccomplished by an eye care professional before an intraocular lenssystem is surgically implanted or after implantation. In someembodiments, post-surgical adjustment may be via a device which allowsthe input or setting of parameters and the transmission of parameters tothe intraocular lens. In some embodiments, the patient may participatein or control post-surgical adjustment in order to fine-tune visionsettings. In some embodiments, default optical characteristics willprovide optical correction for a “distant” vision correction and postsurgical adjustment will modify one or more optical characteristics of“near” vision. However, it is within the scope of this invention tooptical characteristics of both distant and near vision states of amulti-state intraocular lens.

Modifications for focus and adjustment may be independent for eachintraocular lens system, or may be coordinated between intraocular lenssystems worn in both eyes. For example, in some implementations it maybe desirable for focus for both eyes to be determined based on senseddata from one eye. In other situations, it may be optimal for focus tobe independently managed by each intraocular lens system.

Referring now to FIG. 4, an exemplary intraocular lens system isdepicted in a front view block diagram. This embodiment features anintraocular lens system 400 in elliptical form, including a circularvisual zone 401 surrounded by an electrical zone 402. Other embodimentsmay include an optical zone 401 of elliptical, rectangular, or othershape conducive to vision correction. In the present invention, thevisual zone 401 consists of a liquid meniscus lens. A liquid meniscuslens may be in a traditional “hockey puck” form, as shown in FIGS. 1Aand 1B, or in an arcuate form, as shown in FIG. 2.

The intraocular lens system of FIG. 4 includes the same features andcapabilities as the intraocular lens system described in FIG. 3, suchas, for example, ability to change focus, adjustability of settings,electrical zone elements, power management subsystem, charging options,folding capability and encapsulation.

Referring now to FIG. 5, an intraocular lens system 500 is depicted in afront view block diagram. In this embodiment, the intraocular lenssystem 500 is in the form of a circle with a circular visual zone 501surrounded by an electrical zone 502. Other embodiments may include anoptical zone 501 of elliptical, rectangular, or other shape conducive tovision correction. In the present invention, the visual zone 501consists of a liquid meniscus lens. A liquid meniscus lens may be in atraditional “hockey puck” form, as shown in FIGS. 1A and 1B, or in anarcuate form, as shown in FIG. 2.

The intraocular lens system of FIG. 5 includes the same features andcapabilities as the intraocular lens system described in FIG. 3, suchas, for example, ability to change focus, adjustability of settings,electrical zone elements, power management subsystem, charging options,folding capability and encapsulation.

Referring now to FIG. 6, three cross sectional side views ofnon-limiting exemplary intraocular lens systems are depicted. FIG. 6Ashows an embodiment in which an intraocular lens system is flat. Anarcuate version of an intraocular lens system is depicted in FIG. 6B. Anarcuate intraocular lens system may be placed convex toward the exteriorof the eye, or convex toward the interior of the eye. FIG. 6C depicts abiconvex intraocular lens system. FIGS. 6A, 6B and 6C are intended todepict possible embodiments, but do not limit the scope of the inventionas other variations in shape are possible.

What is claimed is:
 1. An intraocular lens system comprising: a frontcurve lens comprising a front curve lens exterior surface and a frontcurve lens interior surface; a back curve lens comprising a back curvelens interior surface and a back curve lens exterior surface said backcurve lens positioned proximate to said front curve lens such that saidfront curve lens interior surface and said back curve lens interiorsurface form a cavity therebetween and forming a lens assembly, saidfront curve lens and back curve lens of suitable size and shape toreplace an intraocular lens in a human eye; a volume of oil and a volumeof saline solution contained within the cavity with a meniscus formedbetween said oil and said saline solution, wherein said meniscuscomprises an optical characteristic; a conductive coating on at least aportion of one or both of said front curve lens interior surface andsaid back curve lens interior surface, said portion comprising aperimeter area of said front curve lens interior surface and said backcurve lens interior surface; a power source for supplying an electricalcharge to the conductive coating, wherein the application of theelectrical charge is sufficient to cause a change of an opticalcharacteristic of said meniscus.
 2. The intraocular lens system of claim1 additionally comprising a processor positioned proximate to the frontcurve lens and the back curve lens, said processor in electricalcommunication to control the application of the electrical charge to theconductive coating.
 3. The intraocular lens system of claim 1additionally comprising an adhesive securing said front curve lens inthe position proximate to the back curve lens, wherein at least one ofsaid front curve lens exterior surface and said back curve lens exteriorsurface comprise an arcuate shape.
 4. The intraocular lens system ofclaim 3 wherein both of said front curve lens exterior surface and saidback curve lens exterior surface comprise an arcuate shape
 5. Theintraocular lens system of claim 1 wherein the power source comprises alithium ion battery.
 6. The intraocular lens system of claim 1additionally comprising a wireless transmitter for communicating logicto and from the processor.
 7. The intraocular lens system of claim 6wherein the communicated logic modifies a focus of the opticalcharacteristic formed by the meniscus.
 8. The intraocular lens system ofclaim 7 wherein the volume of oil is less than the volume of salinesolution contained within the cavity.
 9. The intraocular lens system ofclaim 8 wherein the volume of oil comprises about 66% or more by volumeas compared to an amount of saline solution.
 10. The intraocular lenssystem of claim 8 wherein the volume of oil comprises about 90% or lessby volume as compared to an amount of saline solution.
 11. Theintraocular lens system of claim 10 wherein the conductive coatingextends from an area interior to the cavity to an area external to thecavity.
 12. The intraocular lens system of claim 11, wherein the area ofconductive coating external to the cavity forms an electrical terminalfor providing an electrical charge to the conductive coating based upona signal from the processor.
 13. The intraocular lens system of claim 9wherein the electrical charge comprises a direct current.
 14. Theintraocular lens system of claim 13 wherein the electrical chargecomprises about 20.0 volts.
 15. The intraocular lens system of claim 13wherein the electrical charge comprises between about 18.0 volts to 22.0volts.
 16. The intraocular lens system of claim 13 wherein theelectrical charge comprises about 5.0 volts.
 17. The intraocular lenssystem of claim 13 wherein the electrical charge comprises between about3.5 volts to about 7.5 volts.
 18. The intraocular lens system of claim 3wherein the front curve lens exterior surface comprises an optical powerother than about 0 diopters.
 19. The intraocular lens system of claim 3wherein the front curve lens interior surface comprises an optical powerother than about 0 diopters.
 20. The intraocular lens system of claim 3wherein the back curve lens interior surface comprises an optical powerother than about 0 diopters.
 21. The intraocular lens system of claim 11additionally comprising a channel through one or both of the front curvelens and the back curve lens and a conductive material filling thechannel.
 22. The intraocular lens system of claim 21 additionallycomprising a terminal in electrical communication with the conductivematerial filling the channel.
 23. The intraocular lens system of claim22 wherein application of an electrical charge to the terminal causes achange in the shape of the meniscus.
 24. The intraocular lens system ofclaim 11 additionally comprising an insulator coating along at least aportion of the interior surface of the front curve lens, wherein theinsulator coating comprises an electrical insulator.
 25. The intraocularlens system of claim 24, wherein the insulator comprises one of ParyleneC and Teflon AF.
 26. The intraocular lens system of claim 24 wherein theinsulator comprises a boundary area to maintain separation between theconductive coating and a saline solution contained in the cavity betweenthe front curve lens and the back curve lens.